EP2302952A1 - Auto-ajustement d'un appareil d'aide auditive - Google Patents

Auto-ajustement d'un appareil d'aide auditive Download PDF

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Publication number
EP2302952A1
EP2302952A1 EP09180807A EP09180807A EP2302952A1 EP 2302952 A1 EP2302952 A1 EP 2302952A1 EP 09180807 A EP09180807 A EP 09180807A EP 09180807 A EP09180807 A EP 09180807A EP 2302952 A1 EP2302952 A1 EP 2302952A1
Authority
EP
European Patent Office
Prior art keywords
hearing aid
program
hearing
self
fitting
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP09180807A
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German (de)
English (en)
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EP2302952B1 (fr
Inventor
Ulrich Dr. Giese
Mark Balke
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sivantos Pte Ltd
Original Assignee
Siemens Medical Instruments Pte Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
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Publication date
Application filed by Siemens Medical Instruments Pte Ltd filed Critical Siemens Medical Instruments Pte Ltd
Priority to EP09180807A priority Critical patent/EP2302952B1/fr
Priority to AU2010212415A priority patent/AU2010212415B2/en
Priority to US12/870,964 priority patent/US8848954B2/en
Publication of EP2302952A1 publication Critical patent/EP2302952A1/fr
Application granted granted Critical
Publication of EP2302952B1 publication Critical patent/EP2302952B1/fr
Active legal-status Critical Current
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting

Definitions

  • the invention relates to a method for self-adaptation of a hearing aid by a user to the individual hearing loss of the user. Furthermore, the invention relates to a hearing aid for performing the method.
  • Each hearing aid should be customized to the individual user.
  • the adaptation depends in particular on the hearing loss of the user, geometric factors and the preferences of the user. Thus, measurements and examinations to determine the hearing loss and the geometric factors are required and the personal needs and desires of the user must be questioned.
  • the adaptation of a hearing aid to the individual hearing loss is usually in dialogue between a hearing aid wearer and an acoustician.
  • the hearing aid wearer thereby different test signals are presented, which he perceives subjectively and to whom he shares his impressions with the acoustician.
  • This compares the perception of the hearing aid wearer with the impressions of normal hearing on the respective test signal.
  • the acoustician derives hearing aid device parameter settings, which as a rule lead to an improved adaptation of the hearing aid device to the hearing aid wearer. This procedure is repeated until the hearing-impaired subjectively feels a number of test signals subjectively similar to a normal hearing.
  • EP 1 073 314 A1 a method for individual adaptation of the signal processing of a hearing aid to a user is known in which by means of a measuring device different auditory, involuntary body signals of the user are detected and evaluated for the automatic generation of hearing aid specific fitting parameter settings.
  • the involuntary body signals include, for example, otoacoustic emissions (OAE) or auditory evoked potentials (AEP).
  • OAE otoacoustic emissions
  • AEP auditory evoked potentials
  • Hearing aids can be obtained online from the company America Hears, which are individually programmed in the company on the basis of audiograms that have been sent to the company. For fine adjustment, each user receives a PC program and an interface for his hearing aid. This allows the user to adjust the gain and other features of the signal processing itself.
  • the company "Hearing Help Express” offers an online questionnaire for the selection and setting of a suitable hearing aid.
  • Open supply means that the ear canal is not completely closed by the hearing aid or the earmold of the hearing aid, but remains open to a substantial extent. Thus, even with the supply by the hearing aid still direct sound can reach the eardrum.
  • Object of the present invention is to provide a hearing aid and a method for adjusting a hearing aid that require neither special equipment nor special knowledge or skills in the self-adjustment of the hearing aid.
  • This object is achieved by a method for adapting a hearing aid with the method steps according to claim 1. Furthermore, the object is achieved by a hearing aid with the features of claim 15.
  • a hearing aid according to the invention is understood to mean any device which provides or helps to provide an output signal perceptible by a user as an audible signal and which has means to compensate for an individual hearing loss serve or contribute to the user.
  • these are hearing aids which can be worn on the body or on the head, in particular on or in the ear, and which can be implanted in whole or in part.
  • such devices are also included, whose primary purpose is not to compensate for hearing loss, such as consumer electronics (TVs, hi-fi systems, MP3 players, etc.), or communication devices (mobile phones, PDAs, headsets etc), but over Have means to compensate for an individual hearing loss.
  • An adaptation program in the sense of the invention means a parameter set by means of which the signal processing taking place in the hearing aid device is adapted to the individual hearing loss of the user.
  • parameter settings in particular the determination of the transfer function, i. the gain of an input to the hearing aid input signal in response to the signal frequency.
  • the values of a large number of other parameters can also be defined in an adjustment program. These parameters can, for example, affect the compression, ie the gain as a function of the signal level of the input signal, the noise reduction, the directivity, the feedback suppression, etc.
  • a plurality of fitting programs ie parameter sets are stored with fixed parameter settings.
  • the fitting programs may be derived from the parameter settings resulting from a large number of actual fitting sessions with any hearing-impaired person. For example, different types of deafness may be accounted for by clustering gain and / or compression settings based on a variety of measured audiograms. Providing a limited number of fitting programs in the hearing aid may provide a suitable fit for most in practice occurring hearing losses occur.
  • the parameter settings for the individual fitting programs can be stored in the manufacturer by programming the hearing aid immediately after the production of hearing aids.
  • the method according to the invention enables the user to easily adapt his hearing aid device to his individual hearing loss. There is no need for special knowledge or skills or special equipment for customization.
  • the adaptation of a hearing aid to different listening environments is to be distinguished.
  • the latter is usually done by the choice of a suitable hearing program in which the hearing aid is operated in the respective hearing situation.
  • this also affects the transfer function of a hearing aid and it can also be a manual selection of a suitable hearing program by manual operation of a control by the user.
  • the choice of hearing program can not replace the basic setting of a hearing aid to adapt the signal processing to the individual hearing loss of the user.
  • the parameter sets of the hearing programs for adapting a hearing aid to different, common listening environments or listening situations can be set and programmed immediately after the production of a hearing aid in question at the manufacturer become.
  • the hearing aid is first transferred to a self-tuning mode. This can be done, for example, by the operation of a control element, which can also be attached to a remote control.
  • the Disanpassmodus example, after the first time inserting a battery or after a longer interruption of the power supply, after turning on the hearing aid or set after the operation of a reset switch.
  • the termination of the Disanpassmodus and the change in the normal operation of the hearing aid, wherein the signal processing then takes place in dependence on the selected fitting program can also be performed by the operation of a control by the user or automatically, for example, if for a certain period of time no operation an operating element took place.
  • an adjustment program is preferably initially preset, to which a transfer function with a relatively low, in particular the lowest, gain belongs.
  • the selection may also depend on the previous operating mode. If, for example, the hearing aid device was switched off normally before switching on, then in the self-adjustment mode, the last adjusted adaptation program is activated first. If, on the other hand, a reset switch has been actuated, the predefined fitting program with the lowest gain is subsequently preset.
  • the user then has the ability to select another predetermined fitting program and thus in particular another transfer function.
  • the selection is made via at least one operating element, which is advantageously present on the relevant hearing aid device.
  • the control element can also be located on another device, for example on a remote control for the hearing aid.
  • an already existing on the hearing aid or the remote control control element is used for the selection, for example, the volume control or program selector switch.
  • an operation of the volume control such that an increase in volume would occur in the normal operating mode, lead to the setting of a fitting program and in particular a transfer function with a higher gain compared to the previously set transfer function.
  • an operation of the volume control would be such that in normal operating mode, a reduction of the volume would lead to the setting of a fitting program and in particular a transfer function with a lower gain compared to the previously set transfer function.
  • the adjustment program last set in this manner before leaving the self-adjustment mode is then the selected adaptation program that is decisive for the subsequent operation of the hearing aid.
  • This adaptation program for adapting the hearing aid to the individual hearing loss of the user then remains active until it is changed again by the transfer of the hearing aid into the fitting mode and a re-selection in the manner described.
  • the invention shows its advantages, especially in hearing aids for an open supply. These are ideally suited for the supply of light and medium hearing losses. Mild and moderate hearing losses are usually mainly in the middle and upper frequency range, less noticeable in the low frequency range. Furthermore, in an open supply low-frequency sounds can reach the eardrum almost unhindered. It is therefore usually not necessary to reinforce these sounds especially.
  • the amplification by the open supply relatively narrow physical limits are set. If the gain is too high, more feedback occurs in this frequency range. Because hearing loss in the Frequency range above 2 kHz are usually particularly pronounced, so here the maximum gain can be selected, in which the hearing aid in question still stable, ie can be operated with little feedback tendency.
  • the hearing aid adaptation takes place in an open supply mainly in the middle frequency range of about 500 Hz to about 2 kHz.
  • the transfer functions of the predetermined fitting programs, between which the selection is made by the user differ at least substantially only in the medium transmittable frequency range, e.g. from about 500 Hz to about 2 kHz.
  • the medium transmittable frequency range e.g. from about 500 Hz to about 2 kHz.
  • the overlying frequency range, here above 2 kHz there is always a high, in particular the highest possible gain at which the hearing aid can still be operated safely stable.
  • the transfer function and thus the frequency response of the hearing aid is set for the entire transmittable frequency range.
  • the selection is made in particular by the subjective perception of the user, depending on which of the predetermined fitting programs he feels the greatest help in wearing his hearing aid. They are neither exact measurements in terms of hearing loss still complicated settings required by an audiologist or acoustician.
  • the hearing aid can be supplied from the outside test signals as input signals, e.g. via a computer or a stereo system, or the test signals are stored in the hearing aid or they are generated in an internal signal generator.
  • the supplied test signals are then processed according to the currently adjusted fitting program. If the user is satisfied with it, he ends the self-adjustment mode. Otherwise, he chooses another fitting program.
  • the number of predetermined fitting programs, between which a selection can be made, is essentially limited only by the data memory provided in the hearing aid.
  • the data memory provided in the hearing aid.
  • only 3 different parameter sets can be stored.
  • so many sets of parameters can be stored that the impression of a sliding transition between the different fitting programs arises during the repeated or continuous operation of the relevant control element.
  • the self-adaptation of the hearing aid according to the invention is advantageously supplemented by an individual restriction of the maximum volume, which is generated by the hearing aid.
  • an automatic measurement of the discomfort threshold is preferably carried out, in which, for example, the hearing aid device increases the volume of an acoustic test signal until an operating element is actuated.
  • a limitation of the maximum volume that can be generated by the hearing aid device takes place, at least for a specific frequency range.
  • the compression characteristic that is the dependence of the volume of the output signal on the volume of the input signal, can be influenced by it.
  • inventive self-adaptation is advantageously further supplemented by a measurement of the open loop gain.
  • the measurement result can be used to limit the maximum gain or to configure a feedback suppression device.
  • FIG. 1 shows in a simplified block diagram the structure of a hearing aid, in particular a behind the ear portable hearing aid, according to the prior art.
  • Hearing aids have in principle as essential components at least one input transducer, an amplifier and an output transducer.
  • the input transducer is usually a sound receiver, z. As a microphone, or an electromagnetic receiver, for. B. an induction coil.
  • the output transducer is usually used as an electroacoustic transducer, z. As miniature speaker or handset, or as an electromechanical transducer, z. B. bone conduction, realized.
  • the amplifier is usually integrated in a signal processing unit.
  • FIG. 1 In the embodiment according to FIG. 1 are mounted in a provided behind behind the ear for wearing hearing aid housing 1 a plurality of microphones 2 for receiving the sound from the environment.
  • a signal processing unit 3 which is also located in the hearing aid housing 1, processes the microphone signals and reinforce it.
  • the output signal of the signal processing unit 3 is transmitted to a loudspeaker or earpiece 4, which outputs an acoustic signal. If necessary, the sound is transmitted to the user's eardrum via a sound tube, which is fixed in the ear canal with an earmold.
  • the power supply of the hearing aid and in particular that of the signal processing unit 3 is effected by a battery 5 likewise arranged in the hearing aid housing 1.
  • FIG. 2 Illustrates in a flow chart by way of example a possible procedure for self-adaptation according to the invention:
  • a first step S1 the user learns about the hearing aid and the procedure for self-adaptation. This can be done for example by reading a manual.
  • the hardware is initially adapted.
  • the size of the ear piece which is designed in particular as a universally matching screen (ear tip or dome), to select from a number of different sized ear pieces.
  • the battery is inserted into the hearing aid and the hearing aid is attached to the ear and switched on.
  • the hearing aid automatically recognizes the initial startup and first switches to self-adjustment mode.
  • the hearing aid can also be put into self-adjustment mode at any time by manual actuation of an operating element.
  • the default fitting program which specifies the transfer function with the lowest gain in comparison to the other predefined adjustment programs, is initially preset.
  • the volume control in a further step S4 can then be changed between the different fitting programs.
  • the different fitting programs are ordered in order of increasing gain so that, in keeping with the normal operation of the hearing aid, turning "louder” towards latches with higher gain and turning “louder” will result in lower gain latches ,
  • the user may hear an audible signal through the hearing aid.
  • the signal processing for the acoustic signal in accordance with the currently set fitting program.
  • the user can therefore immediately recognize the effects of different adaptation programs on the signal processing.
  • the acoustic signal can be generated outside of the hearing aid or stored in the hearing aid or can only be generated in the hearing aid.
  • the Edanpassmodus is terminated in a further step S5 either by the manual operation of a control element or automatically, if none of the hearing aid controls is pressed in Organicanpassmodus for a certain period of time.
  • the fitting program last selected in the self-adjustment mode is then decisive for the further signal processing.
  • the fitting program selected in this way is also decisive after switching the hearing device off and on again.
  • the first selection of a fitting program can be followed by a training phase in a further step S6.
  • the training phase causes the last selected fitting program is not the only relevant fitting program, but that the "history", ie previously selected fitting programs have an influence on the currently performed by the hearing aid signal processing.
  • the period of time for which the adjustment program relevant prior to the last change was retained determines to what extent previously selected adjustment programs still have an influence on the currently relevant parameter set.
  • the user selects a fitting program and keeps it for a long period of time, for example, for several weeks. Then he selects another predetermined fitting program with a much higher gain. This will be activated immediately.
  • the hearing aid After switching off and on again the hearing aid is automatically determined by the hearing aid, a new fitting program in which the parameter settings are substantially the same as those of the long-held fitting program, but slightly approximate the parameter settings of the last adjusted fitting program.
  • the hearing device learns the changed user behavior and also after switching off and on again, a fitting program with a correspondingly high gain. The hearing aid thus learns the preferences of the user, with individual and / or only short-term changes in the selection of a suitable fitting program not significant.
  • the hearing aid In the training phase, it is possible that only predetermined fitting programs with the associated parameter sets can be set by the hearing aid. Alternatively, it is also possible for the hearing aid to allow intermediate values for the given parameter sets during the automatic determination of parameter settings during the training phase.
  • an individual adaptation of the maximum Output power and / or compression take place.
  • This is preferably accompanied by a measurement of the discomfort threshold, to which preferably different loud test signals are output by the hearing device and the reactions of the user are detected.
  • Narrow-band noise in particular in the relevant frequency range between 500 Hz and 2 kHz, in which the volume is increased step by step, is suitable as the test signal.
  • the volume of the last generated signal then gives the discomfort threshold.
  • the gain or compression related parameters are then automatically adjusted so that the discomfort threshold is not exceeded.
  • the extension of the self-adaptation to the adjustment of the maximum output power and / or the compression further individualises the hearing aid fitting and takes account of safety aspects.
  • the procedure required for self-adaptation is advantageously described in an instruction manual distributed together with a corresponding hearing aid. This can also be stored on a data medium with the associated multimedia options, e.g. Graphics, videos etc, to be saved.
  • the self-adaptation according to the invention is so simple that a brief description of the procedure in paper form is generally sufficient.
  • the invention offers the advantage that the user can carry out the adaptation of the signal processing taking place in the hearing device to his own individual hearing loss. He can make these in his preferred, real listening environments and thus outside of artificial listening environments, as they are available for adaptation in a hearing care professional. This leads to better results in the adjustment. Neither an audiometer nor an adapter is required, and the time required for conventional adaptation is eliminated. The adaptation according to the invention takes place without special device or specialist personnel. It can be repeated at any time.
  • FIG. 3 8 different transfer functions of the hearing aid according to the invention, represented by the associated transfer characteristics, can be seen. Shown is the gain P over the frequency f on the basis of a logarithmic frequency scale.
  • the transfer characteristics are provided with the reference numerals 11 to 18, to which the transfer functions are assigned in the order of the reference numerals with increasing gain. That is, the transfer characteristic 11 belongs to the transfer function with the lowest gain and the transfer characteristic 18 belongs to the transfer function with the highest gain with respect to a broadband input signal with a certain signal level.
  • the 8 transmission characteristics belong to 8 predetermined and selectable fitting programs, by the choice of which the user can adapt the respective hearing device to his individual hearing loss.
  • a large number of further parameter settings of the respective hearing device can be predefined by the respective fitting program. These parameter settings may include, for example, compression, noise reduction, directivity, or feedback suppression.
  • the hearing aid is in the self-adjustment mode, it is possible to switch between the different fitting programs and thus between the different transfer functions. For example, can be transferred to the transfer functions with higher or lower gain by the operation of the volume control of the hearing aid. It is also possible that, for example, in a hearing aid with 8 hearing programs for different listening environments, which can be set directly by 8 program selection buttons on a remote control, the 8 program selection buttons in Dianpassmodus directly to select a fitting program.
  • the transmission characteristics differ mainly in the frequency range between a lower threshold F1, in the embodiment at 500 Hz, and an upper threshold F2, in the embodiment at 2 kHz.
  • Below threshold F1 much of the amplified sound is lost through the vent of the hearing aid. All the more so, the bigger the vent is and especially with an open supply. Therefore, with an open supply with a gain below 500 Hz, little can be achieved anyway.
  • an area B1 hatchched
  • a high gain is required due to the dominant in this frequency range hearing loss of most hearing impaired.
  • the gain in this frequency range is limited by the stability of the hearing aid in terms of feedback.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
EP09180807A 2009-08-28 2009-12-28 Auto-ajustement d'un appareil d'aide auditive Active EP2302952B1 (fr)

Priority Applications (3)

Application Number Priority Date Filing Date Title
EP09180807A EP2302952B1 (fr) 2009-08-28 2009-12-28 Auto-ajustement d'un appareil d'aide auditive
AU2010212415A AU2010212415B2 (en) 2009-08-28 2010-08-18 Self-adjustment of a hearing aid
US12/870,964 US8848954B2 (en) 2009-08-28 2010-08-30 Self-adjustment of a hearing aid and hearing aid

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP09168936 2009-08-28
EP09180807A EP2302952B1 (fr) 2009-08-28 2009-12-28 Auto-ajustement d'un appareil d'aide auditive

Publications (2)

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EP2302952A1 true EP2302952A1 (fr) 2011-03-30
EP2302952B1 EP2302952B1 (fr) 2012-08-08

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EP09180807A Active EP2302952B1 (fr) 2009-08-28 2009-12-28 Auto-ajustement d'un appareil d'aide auditive

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US (1) US8848954B2 (fr)
EP (1) EP2302952B1 (fr)
AU (1) AU2010212415B2 (fr)
DK (1) DK2302952T3 (fr)

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EP3267695B1 (fr) 2016-07-04 2018-10-31 GN Hearing A/S Balayage automatisé des paramètres pour prothèse auditive

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US9679403B2 (en) * 2008-12-18 2017-06-13 Xerox Corporation Method and system for utilizing transformation matrices to process rasterized image data
DE102011087569A1 (de) * 2011-12-01 2013-06-06 Siemens Medical Instruments Pte. Ltd. Verfahren zum Anpassen einer Hörvorrichtung durch eine formale Sprache
EP2901716A1 (fr) * 2012-09-27 2015-08-05 Jacoti BVBA Méthode de réglage des paramètres d'une fonctionnalité d'audioprothèse fournie dans un dispositif électronique grand public
WO2014094866A1 (fr) * 2012-12-21 2014-06-26 Widex A/S Système de pose de prothèse auditive, et procédé pour la pose d'un système de prothèse auditive
US10382872B2 (en) 2017-08-31 2019-08-13 Starkey Laboratories, Inc. Hearing device with user driven settings adjustment

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WO2000078096A2 (fr) 1999-06-15 2000-12-21 Sarnoff Corporation Prothese auditive a format acoustique
EP1073314A1 (fr) 1999-07-27 2001-01-31 Siemens Audiologische Technik GmbH Procédé d'adaptation d'une prothése auditive et prothése auditive
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WO2009053517A1 (fr) 2007-10-25 2009-04-30 Jose Benito Caballero Catoira Système pour le relevé à distance de mesures audiométriques et l'ajustement d'audiophones par l'intermédiaire du réseau internet

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3267695B1 (fr) 2016-07-04 2018-10-31 GN Hearing A/S Balayage automatisé des paramètres pour prothèse auditive

Also Published As

Publication number Publication date
AU2010212415A1 (en) 2011-03-17
US8848954B2 (en) 2014-09-30
AU2010212415B2 (en) 2012-11-29
US20110051964A1 (en) 2011-03-03
EP2302952B1 (fr) 2012-08-08
DK2302952T3 (da) 2012-11-19

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